Neural bridge gateway and calibrator

ABSTRACT

A device for communicating data between at least one of nerve cell endings, transducers and attachments the device comprising: at least one programmable neural bridge device; at least one programmable neural bridge switch, wherein each programmable neural bridge switch is an implanted integrated circuit and is connected to at least one programmable neural bridge device; at least one programmable neural bridge gateway; at least one communication means in communication with the at least one programmable neural bridge gateway and at least one programmable neural bridge switch; and at least one external calibrator in communication with at least one neural bridge gateway.

This application claims priority to application No. 60/862,488 as filedon Oct. 23, 2006 and application No. 60/862,503 filed on Oct. 23, 2006.

BACKGROUND OF THE INVENTION

The present invention relates to several art areas. In one aspect, theinvention relates to the recent achievements in building small-scale,micro and nano-size, electromechanical apparatuses and computingcomponents. According to another aspect, the main application of theinvention is to facilitate restoring the functionality of an impairedhuman nervous system. In still other aspect, the invention may modulatethe activity of the nervous system.

The evolving area of micro-electromechanical systems (“MEMS”) makes itpossible to assemble complex functioning mechanical devices on a levelwhich may not even be recognized by unaided human eye. The dominantportion of new developments in the area of MEMS is geared toward thecomputer industry, such as development of micro- and nano-scalenon-volatile memory, batteries, magnets, capacitors, and motors.

It is generally accepted that the human nervous system consists of thebrain, the spinal cord and nerves. A nerve cell is an elementarybuilding block of the nervous system. A nerve cell generally has threeidentifiable regions: a cell body, or soma, short outgrowths, ordendrites, and a long outgrowth, or an axon. There are a great varietyof nerve cells characterized primarily by the difference in thedimension of axon part and the localization of a cell body.

Some nerve cells have all theirs parts located in a single place such asthe brain. Other cells have their axons running substantial distances.For instance, the axon may run from the brain along the entire length ofa spinal cord. The axon is primarily responsible for conducting signalsfrom one nerve cell to another or for conducting stimulus to and fromother organs. Further, the nerve cells whose axons run from and to thebrain along the spinal cord interact with other nerve cells, includingperipheral nerves, whose cell bodies are primarily located in the socalled spinal roots or dorsal ganglia. The nervous system also makessure that organs and tissues, such as muscles, function properly.

The peripheral nerves are primarily divided into three main groups: (1)sensory, or afferent, (2) motor, or efferent, and (3) nerves of theautonomic system. Further, the nerves in each group are generallysubdivided based on the diameter of axon, or a conducting fiber.

An inactive axon usually has a small negative potential, a restingpotential, inside the cell due to distribution of ions inside andoutside of the axon. An a nerve impulse starts generally when a nervecell experiences an increased influx of ions, usually sodium ions whichleads to depolarization of inner cell membrane of an axon for a shortperiod of time. The depolarization at a particular place in the axon, ifit is strong enough, would propagate itself into neighboring regions,generally, by diffusion of sodium ions. Immediately, the increasedinflux of sodium ions provokes the increased outflow of potassium ionsat the place to where the initial impulse came in. In a short period, atthe initial place of excitation the system returns to equilibrium, whilethe depolarization, i.e. the impulse continues to travel along the axon.

Some axons, generally referred to as white matter, stretching forsubstantial distances, have special shielding material around them whichis interrupted by small portions of a naked nerve cell. In such axons,it is believed that the depolarization can only occur at the nakedsections allowing the impulse to travel long distances withoutsubstantial decrease in its depolarizing ability. Unfortunately, manydiseases and injuries may lead to partial or complete severance of theneural conductive pathways, i.e. axons.

For instance, one such injury is a spinal cord injury which could resultwhen a person experiences a catastrophic fall, such as being thrown froma horse or being in a severe car accident. Depending on the area of thespinal cord, the injury may even lead to total paralysis of hands andlegs, known as quadriplegic condition. Many thousands of spinal cordinjuries occur in the United States each year. It is estimated that itgenerally costs over four billion dollars to care for people with spinalcord injuries.

There have been many attempts to address the problem of a severed nervecell. Some attempts concentrate on different ways to secure the severedends together. Another attempt, in addition to securing both ends of anaxon, propose using electro-charged surfaces or surfaces covered withdifferent chemical and biological compositions to stimulate theregeneration. Still other attempts propose uniting the severed ends andusing microelectrodes to stimulate the neural endings from an outsidesource.

While the proposed solutions may provide for a way to hold ends of asevered nerve, they do not overcome a pivotal problem of supporting thepropagation of action potential from a primary end to another. Further,many proposed solutions add a substantial outside structure over asevered nerve which may exert negative pressure on the neighboringnerves and other tissue.

U.S. Pat. No. 4,308,868, entitled “Implantable electrical device”discloses a fully implantable and self-contained device composed of aflexible electrode array 10 for surrounding damaged nerves and a signalgenerator 12 for driving the electrode array with periodic electricalimpulses of nanoampere magnitude to induce regeneration of the damagednerves.

U.S. Pat. No. 5,314,458, entitled “Single channel microstimulator”discloses an implantable microstimulator system employs a miniatureferrite-cored coil contained with an hermetically sealed housing toreceive control signals and operating power from an RF telemetry system.The tiny coil receives the electromagnetic energy which is transmittedfrom a non-implantable transmitter which generates a code-modulatedcarrier. Demodulator circuitry in the implantable microcircuit isemployed to extract the control information, while applying theelectromagnetic energy to power the electronic circuitry therein andcharge a capacitor which will provide the electrical stimulation to theliving being. The electrical stimulation is delivered by a stimulatingelectrode which has a waffle-like configuration whereby a plurality ofiridium oxide electrode pads, coupled in parallel, so as to becharacterized by a long effective edge distance, transfer thestimulating charge. The electrical components of the implantablemicrostimulator are contained within an hermetically sealed housingformed of a glass capsule which is electrostatically bonded to a siliconsubstrate.

U.S. Pat. No. 5,030,225, entitled “Electrically-charged nerve guidancechannels” discloses a medical device is disclosed for use inregenerating a severed nerve. The device includes an implantable,tubular, electrically-charged membrane having openings adapted toreceive the ends of the severed nerve and a lumen having a diameterranging from about 0.5 millimeters to about 2.0 centimeters to permitregeneration of the nerve therethrough. The membrane is fabricated suchthat an electric charge is exhibited at the inner membrane surface tostimulate regeneration by axonal sprouting and process extension. Alsodisclosed are methods for repairing a severed nerve and for preparing amedical device for use in regeneration of a severed nerve.

U.S. Pat. No. 4,878,913, entitled “Devices for neural signaltransmission” discloses devices and methods for transmitting neuralsignals from a proximal stump of a transected nerve to a prostheticapparatus are disclosed employing microelectrodes, preferably conductivefiber networks, capable of sensing electrical signals from a nerve andtransmitting such signals to a prosthetic apparatus; and a semipermeableguidance channel disposed about the microelectrodes. The channelsinclude an opening adapted to receive the proximal stump of a transectednerve, such that the channel promotes the growth of the stump and theformation of an electrical connection between the transected nerve andthe microelectrode.

U.S. Pat. No. 6,235,041, entitled “Medical device for treatment of a gapor defect in the central nerve system” discloses a medical device (1) ofa biocompatible material for use in the treatment of a gap or defect inthe central nervous system, which device has a proximal end (5) and adistal end (6) comprising openings (7). The device is adapted to enableconnection of nerve fibers of gray and white matter between the proximalend (5) and distal end (6) thereof in predetermined openings (7). Thedevice is of a substantially cylindrical form, or a substantially flator plate like form and is made of plastic. The openings (7) in at leastone end (5, 6) bear distinctively different indicia thereby to indicatewhether nerve fibers of gray matter or nerve fibers of white matter areto be inserted therein.

U.S. Pat. No. 5,354,305, entitled “Nerve repair device” discloses anerve repair device which includes a resilient, elongated implant, andtransverse pins for retaining the implant fixedly within the ends of thesevered nerve. A sharp tip extends longitudinally from at least one endof the elongated implant, and aids in the insertion of the implantlongitudinally through the ends of the severed nerve between thefascicle bundles. The severed ends are retained in close approximationfor reconnection.

U.S. Pat. No. 4,778,467, entitled “Prostheses and methods for promotingnerve regeneration and for inhibiting the formation of neuromas” isdirected to prosthesis and methods for promoting nerve regeneration. Theproximal and distal ends of a severed nerve are brought into closeproximity and are enclosed by a tubular prosthesis. In one preferredembodiment, a epineurial or endoneurial monosuture is used to hold thenerve ends in close proximity. A tight seal is formed between theprosthesis and the injured nerve so as to isolate the injured nervewithin the prosthesis from the rest of the body of the host.Additionally, in one preferred embodiment, nerve grafts may beincorporated into the prosthesis and nerve regeneration promotingsubstances may be incorporated within the nerve graft to further enhancenerve regeneration. In another preferred embodiment, a prosthesis iscoated with a material which is slippery with relation to thesurrounding body tissue and the prosthesis is formed of or coated with amaterial around the inside of the prosthesis which will substantiallyadhere to the severed nerve ends so as to prevent substantial movementof the severed nerve ends within the prosthesis. In yet anotherpreferred embodiment, such an outside coating around the prosthesisterminates in two longitudinal flaps which serve to form a fluid-tightseal along the tubular prosthesis. In still another preferredembodiment, the ends of the prosthesis overlap and are formed so as tobias against each other in a spiral tube configuration, therebyproviding for firm closure of the prosthesis around a variety of sizesof injured nerves. Also disclosed are various devices and methods forinhibiting the formation of neuromas, such as an open-ended tube or aneuroma-inhibition device formed as a cap member having a reservoirformed therein.

U.S. Pat. No. 4,306,561, entitled “Holding apparatus for repairingsevered nerves and method of using the same” discloses circumferentiallyembracing both the proximal and distal portions of a severed nerve atpositions removed from the severed ends and controllably moving thesevered portions into abutting, juxtaposed contacting relationship, thereattachment and repair of severed nerves is achieved. Preferably, bothportions of the severed nerve are embraced within a holding member whichincorporates nerve securing means at the desired location. In addition,the preferred nerve holding member incorporates nerve coolingcomponents, electrical pulse stimulation means for directing a pulsefrom the proximal portion towards the distal portion, and temperaturesensing components for monitoring the temperature of the nerve.

U.S. Pat. No. 5,038,781, entitled “Multi-electrode neurologicalstimulation apparatus” discloses an implantable system for FunctionalElectro-Stimulation (FES), which includes an environmentally sealedimplant case and a nerve cuff for attaching to the nerve. A plurality ofleads connect the nerve cuffs to the case. The implant case providesredundant seals for entrance of the leads in a double wall/doubleenvironmental seal to provide long term sealing reliability for thecase. Inside the case, the wires in each lead attach to connectors,which establish contact with an enclosed master circuitry case. Theconnectors allow the leads to be individually removed and replaced,thereby providing a maintainable system. At the other end of the leadsis attached the nerve cuff. Each nerve cuff has a hollow, gappedcylindrical shape, and includes electrodes on its inner surface. Thecuff is deformable to allow placement around the nerve, holding theelectrodes in electrical contact therewith. In other embodiments of theinvention, the nerve cuff includes a micro circuit which is capable ofdemultiplexing stimulation signals from a single pair of wires in thelead to drive multiple electrodes. These embodiments reduce the numberof wires needed in each lead to facilitate the stimulation of a largenumber of nerves with a single implant.

U.S. Pat. No. 5,300,096, entitled “Electromyographic treatment device”discloses an electrical muscle stimulator converts electromyographic(EMG) signals to digital words for analysis and display by a computerprogram. The therapist selects a variety of different parametersappropriate for the individual patient, and instructs the device toinitiate stimulating signals on command, or upon detection of a suitableEMG signal from the patient. The device that converts digital wordsrepresenting the selected parameters into complex, bipolar therapeuticpulses. The device can digitally model a wide variety of wave forms andgraphically assist the therapist in developing and shaping various wavepulse trains.

U.S. Pat. No. 5,041,974, entitled “Multichannel stimulator for tunedstimulation” discloses a multichannel stimulator device having a hostuser interface circuit for enabling a user to select a channel andeasily create and display a stimulus wave signal for the selectedchannel and generate a data signal specifying the channel and stimuluswave signal. The stimulator also includes a master circuit for receivingthe data signal and directing it to the specified channel as a wavebuilding instruction signal. A slave circuit associated with the channelspecified receives the wave building signal and responds by generating acorresponding low power stimulus wave signal in the channel specified.Then an output circuit coupled to the slave circuit electricallyisolates the low power stimulus wave signal from other channels,amplifying and converting it to a corresponding high fidelity currentstimulus wave signal.

U.S. Patent Application No. 20040024439 entitled “Nerve cuff electrode”discloses a nerve electrode system for stimulating and/or monitoring atleast one nerve fascicle in a trunk nerve comprising at least oneinternal electrode and at least one external electrode. The inventionalso relates to a multi-polar nerve cuff, a method of installing a nerveelectrode system or a multi-polar nerve cuff and finally the inventionrelates to uses of the nerve electrode system or the multi-polar nervecuff.

U.S. Patent Application No. 20020120309, entitled “System and method forproviding recovery from muscle denervation”. Recovery from peripheralnerve and nerve plexus injuries is usually slow and incomplete becausethe regenerating motor axons often head erroneously toward sensoryreceptors rather than muscle fibers and because the target musclesatrophy while waiting for the slow process of reinnervation. Researchhas suggested that electrical stimulation with different waveforms andtemporal patterns at different times during the regeneration processmight improve the clinical outcome through various mechanisms, but apractical means to deliver such stimulation has been lacking. Thisinvention teaches the use of miniature electrical stimulators that canbe implanted alongside the injured nerve(s) at the time of surgicalrepair and that can be powered and controlled by transmission ofradiofrequency energy from outside the body so as to provide a varietyof electrical stimuli at different times during the recovery process.

U.S. Patent Application No. 20030176876, entitled “Multi-channelbioresorbable nerve regeneration conduit and process for preparing thesame” discloses a multi-channel bioresorbable nerve regeneration conduitand a process for preparing the conduit. The multi-channel bioresorbablenerve regeneration conduit includes a hollow round tube of a porousbioresorbable polymer and a multi-channel filler in the round tube. Themulti-channel filler is a porous bioresorbable polymer film with anuneven surface and is single layer, multiple layer, in a folded form, orwound into a spiral shape.

U.S. Patent Application No. 20030153965, entitled “Electricallyconducting nanocomposite materials for biomedical applications”discloses exposing osteoblasts on an electrically conductingnanocomposite, which may be an orthopaedic/dental implant, to electricalstimulation enhances osteoblast proliferation thereon. The electricallyconducting nanoscale material includes an electrically conductingnanoscale material and a biocompatible polymer and/or a biocompatibleceramic; carbon nanotubes may be used as the electrically conductingnanoscale material.

U.S. Patent Application No. 20010031974, entitled “Neural regenerationconduit” discloses a neural regeneration conduit employing spiralgeometry is disclosed. The spiral geometry is produced by rolling a flatsheet into a cylinder. The conduit can contain a multiplicity offunctional layers lining the lumen of the conduit, including a confluentlayer of adherent Schwann cells. The conduit can produce a neurotrophicagent concentration gradient by virtue of neurotrophic agent-ladenmicrospheres arranged in a nonuniform pattern and embedded in a polymerhydrogen layer lining the lumen of the conduit.

U.S. Patent Application No. 20020193858 entitled “Miniature implantableconnectors” discloses methods of making electrical connections in livingtissue between an electrically conductive wire and an implantableminiature device. The device may either stimulate muscles or nerves inthe body or detect signals and transmit these signals outside the bodyor transmit the signals for use at another location within the body. Thedevice is comprised of an electrically insulating or electricallyconductive case with at least one electrode for transmitting electricalsignals. The electrodes and the wire-electrode connections are protectedfrom the aggressive environment within the body to avoid corrosion ofthe electrode and to avoid damage to the living tissue surrounding thedevice.

U.S. Patent Application No. 20040015205 entitled “Implantablemicrostimulators with programmable multielectrode configuration and usesthereof” discloses miniature implantable stimulators (i.e.,microstimulators) with programmably configurable electrodes allow, amongother things, steering of the electric fields created. In addition, themicrostimulators are capable of producing unidirectionally propagatingaction potentials (UPAPs).

U.S. Patent Application No. 20040015204 entitled “Implantablemicrostimulators and methods for unidirectional propagation of actionpotentials” discloses miniature implantable stimulators (i.e.,microstimulators) are capable of producing unidirectionally propagatingaction potentials (UPAPs). The methods and configurations described may,for instance, arrest action potentials traveling in one direction,arrest action potentials of small diameters nerve fibers, arrest actionpotentials of large diameter nerve fibers. These methods and systems maylimit side effects of bidirectional and/or less targeted stimulation.

U.S. Patent Application No. 20030181956 entitled “Multi-purpose FESsystem” discloses a multi-purpose FES system which includes amulti-function, implantable stimulator for stimulating different sitesin a patient's body. The stimulator includes a control unit and areceiving device. The stimulator further has a plurality of bundles ofelectric leads connected to the control unit, each lead terminating inat least one electrode to provide a plurality of discrete groups ofelectrodes associated with each site. Each group of electrodes isoperable to stimulate its associated site in the patient's body, underthe action of stimulation signals from the control unit, the controlunit receiving signals from the receiving device. A transmitter isarranged externally of the patient's body for supplying signalstranscutaneously to the receiving device of the stimulator. A controlleris in communication with the transmitter via a communications interfaceunit.

U.S. Patent Application No. 20030171785 entitled “Distributed functionalelectrical stimulation system” discloses a multi-purpose, functionalelectrical stimulation (FES) system includes an implantable stimulatorunit for stimulating a plurality of different sites in a patient's body.A transmitter is arranged externally of the patient's body for supplyingsignals transcutaneously to the stimulator unit. A controller is incommunication with the transmitter. At least one implantable switchingnode has an input terminal in electrical communication with thestimulator unit and a plurality of output terminals to each of which oneof a further switching node and a stimulating element is connected. Theswitching node including addressing circuitry for switching at least oneoutput terminal into electrical connection with the input terminal ofthe switching node in response to a control signal received from thecontroller via the stimulator unit.

U.S. Patent Application No. 20030149457 entitled “Responsive electricalstimulation for movement disorders” discloses an implantableneurostimulator system for treating movement disorders includes asensor, a detection subsystem capable of identifying episodes of amovement disorder by analyzing a signal received from the sensor, and atherapy subsystem capable of applying therapeutic electrical stimulationto treat the movement disorder. The system treats movement disorders bydetecting physiological conditions characteristic of an episode ofsymptoms of the movement disorder and selectively initiating therapywhen such conditions are detected.

U.S. Patent Application No. 20030144710 entitled “Method and implantablesystems for neural sensing and nerve stimulation” discloses an inventionwhich relates to methods and apparatuses for the detection of neural ormuscular activity, analysis of the signals and the subsequentstimulating of neural or muscular tissue based thereon. According to afirst aspect of the invention an apparatus for producing a muscularaction is provided, comprising a combined sensing and stimulationelectrode device comprising at least one neurosense electrode meanscapable of sensing a nerve signal from a peripheral nerve and at leastone stimulation electrode means capable of stimulating a peripheralmotor nerve fibre, means for receiving and processing the sensedneurosignals to identify a signal indicative of a specific action,especially a component of the gait performed by the patient and forproducing a control signal in response thereto, and means for operatingthe at least one stimulation electrode means in response to the controlsignal to produce a stimulation of a peripheral motor nerve fibre.

U.S. Patent Application No. 20010000187 entitled, “Functionalneuromuscular stimulation system” discloses an input command controller(A) provides logic function selection signals and proportional signals.The signals are generated by movement of a ball member (12) and socketmember (14) relative to two orthogonal axes. When the joystick isimplanted, a transmitter (50) transmits the signals to a patient carriedunit (B). The patient carried unit includes an amplitude modulationalgorithm such as a look-up table (124), a pulse width modulationalgorithm (132), and an interpulse interval modulation algorithm (128).The algorithms derive corresponding stimulus pulse train parameters fromthe proportional signal which parameters are transmitted to an implantedunit (D). The implanted unit has a power supply (302) that is powered bythe carrier frequency of the transmitted signal and stimulation pulsetrain parameter decoders (314, 316, 318). An output unit (320) assemblespulse trains with the decoded parameters for application to implantedelectrodes (E). A laboratory system (C) is periodically connected withthe patient carried unit to measure for changes in patient performanceand response and reprogram the algorithm accordingly. The laboratorysystem also performs initial examination, set up, and other functions.

U.S. Patent Application No. 20030208246 entitled “Electrostimulationsystem with electromyographic and visual biofeedback” provided anelectrostimulation system with electromyographic and visual biofeedbackfor sensing electromyographic impulses and facilitating muscularactivity. The electrostimulation system comprises stimulator that isadapted to generate an electric impulse and at least one pair ofelectrodes adapted to transmit the electric impulse or to receiveelectromyographic impulses. The system further comprises an amplifierelectrically communicating with the pair of electrodes, the amplifier isadapted to amplify the received electromyographic impulses and afiltering unit electrically communicating with the amplifier and isadapted to remove artifacts from the received electromyographic impulse.A commutation block is electrically communicating with the pair ofelectrodes and is adapted to alternately transfer the electromyographicimpulses to the amplifier or to transfer the generated electric impulsefrom the stimulator. A display for displaying the receivedelectromyographic impulses and a predetermined threshold value is alsoprovided as well as a control unit that is adapted to receive theelectromyographic impulses from the amplifier and to activate thestimulator in a predetermined manner. The stimulator incorporated in thepresent invention is triggered to transmit impulses to the rehabilitatedmuscle when the electromyographic impulse substantially equals orexceeds the predetermined threshold value.

One type of prior art solution attempts to deal directly with theaftermath of a spinal cord injury by trying to somehow repair thesevered nerve cells. Another type of prior art solution concentrates onaddressing the consequences of a spinal cord injury such as theinability of an injured person to control bodily functions below theinjured area. Such solutions propose external micro-stimulators whichare placed around or embedded into one or several peripheral nerves andwhich stimulate those nerves in accordance with a necessary regime.

Most solutions consist of a conducting plate or a plurality ofmicro-electrodes. Some solutions propose a system in whichmicro-stimulating an implant may have power generating and storingability, an ability to communicate, and an ability to affect thepropagation of action potential in a nerve.

However, implant systems have certain disadvantages. One disadvantage isan implant imposes a substantial outside structure over a nerve. Thenerve may exert negative pressure on the neighboring nerves and othertissue. Another disadvantage is that such implant is unable to fullyfunction autonomously because of its inability to convert theelectrochemical energy of an action potential into an electrical power.Still other disadvantage is that such a system lacks the functionalityto read the nerve cell own action potentials and to produce or modulatethe action potentials based on these readings without reserving to anyexternal communications.

These and other features, aspects and advantages of the presentinvention will become better understood with reference to the followingdescription and claims.

SUMMARY OF THE INVENTION

The present invention provides a device and methods for sensing andcommunicating nerve cell endings and neural signals.

According to one aspect of the invention, a device for sensing andcommunicating nerve cell endings and neural signals is provided, thedevice comprising: at least one neural bridge device; at least oneneural bridge switch, wherein each neural bridge switch is an implantedintegrated circuit and is connected to at least one neural bridgedevice; at least one neural bridge gateway; at least one communicationmeans in communication with at least one neural bridge gateway and atleast one said neural bridge switch; at least one sensory interfaceintegrated circuit in communication with said at least one neural bridgeswitch; at least one transducer in communication with said at least onesensory interface integrated circuit; and at least one attachment meansin communication with said at least one transducer.

According to another aspect of the invention, a method of communicatingaction potentials between at least one of nerve cell endings, spinalcord, brain and neural signals of a user is provided, the methodcomprising the steps of: providing at least one neural bridge device;providing at least one neural bridge switch, wherein each said at leastone neural bridge switch is an implanted integrated circuit and isconnected to at least one neural bridge device; providing at least oneneural bridge gateway; providing at least one communication means incommunication with said at least one neural bridge gateway and at leastone said neural bridge switch; providing at least one sensory interfaceintegrated circuit in communication with said at least one neural bridgeswitch; providing at least one transducer in communication with said atleast one sensory interface integrated circuit; and providing at leastone attachment means in communication with said at least one transducer,wherein at least one said sensory interface integrated circuit receivesat least one sensory signal from said transducer and translates saidsignal to at least one standardized digital signal.

According to still other aspects of the invention, the inventionincludes a method for modulating nerve signals or responses. The varioustypes of neural bridge devices carrying some or all of the MEMS devicesare secured between the first end of a severed nerve and the second endof a severed nerve. The desired signals are communicated to the devicesby any suitable means. The neural bridge device modifies receiving nervesignals in accordance with the desired signals communicated to thesedevices. In some aspects of the invention, the devices communicate thesignals away from the devices by any suitable means. In still otheraspects of the invention, the devices communicate the desired signalsamong each other in synchronous or asynchronous manner. In still furtheraspects of the invention, the devices modify nerve responses outside aparticular nerve cell containing one or many neural bridge devices.

These and other features, aspects and advantages of the presentinvention will become better understood with reference to the followingdescription and claims.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a diagram according to one aspect of the present invention;

FIG. 2 is a diagram according to one aspect of the present invention;

FIG. 3 is a diagram according to one aspect of the present invention;

FIG. 4 is a diagram according to one aspect of the present invention;

FIG. 5 is a diagram according to one aspect of the present invention;

FIG. 6 is a diagram according to one aspect of the present invention;

FIG. 7 is a diagram according to one aspect of the present invention;

FIG. 8 is a diagram according to one aspect of the present invention;

FIG. 9 is a diagram according to one aspect of the present invention;

FIG. 10 is a diagram according to one aspect of the present invention;

FIG. 11 is a diagram according to one aspect of the present invention;

FIG. 12 is a diagram according to one aspect of the present invention;

FIG. 13 is a diagram according to one aspect of the present invention;

FIG. 14 is a diagram according to one aspect of the present invention;

FIG. 15 is a diagram according to one aspect of the present invention;and

FIG. 16 is a diagram according to one aspect of the present invention.

DETAILED DESCRIPTION OF THE INVENTION

The present invention is capable of many different embodiments, andmodifications in various respects, all without departing from thepresent invention. Accordingly, the drawings and description are to beconsidered as illustrative in nature, and not as restrictive.

The present invention may be employed for the treatment of variousmedical conditions in which the continuity of nerve cells, for examplethe axon part of a cell, is destroyed due to a disease or an injury. Oneexample of such an injury may be a spinal cord injury. In thisimplementation, the method may consist of providing a housing devicewhich may be implanted into a place of an injury by connecting the firstend of the device to a primary end of a severed axon and connecting thesecond end of the device to a secondary end of the severed axon. In thisrespect, the device serves as a bridge between two severed ends. Thedevice may use the cell's condition of active potential on a primary endof the device, generate electrical power, and use this electrical powerto initiate action potentials on a secondary end of the device. Fluidsmay be transported between the first nerve ending and the second nerveending. It is envisioned that multiple neural devices or neural bridgesmay be required and there may need to be communication among thedevices. Data may need to be communicated for status, command, control,electrical power distribution, neural intracellular fluid distributionand optionally action potentials.

One advantage of the present invention is that it provides a number ofdevices that do not impose any substantial outside structure over anerve which may exert negative pressure on the neighboring nerves andother tissue. Another advantage is that the device may be able tofunction fully autonomously because of its ability to convert theelectrochemical energy of an action potential into an electrical power.Still other advantage is that the invention is able to read the nervecells own action potentials and produce or modulate the actionpotentials based on these readings without reserving to any externalcommunications.

The invention will be now illustrated in reference to the accompanyingdrawings. FIG. 1 depicts a block diagram according to a preferredembodiment of the present invention. In some preferred embodiments andmethods of operation, the neural bridge device made in accordance withthe invention, FIG. 1, may incorporate a housing 100 having a first end115, a second end 116 and a cavity. The diameter of the housing 100 mayvary from approximately 1 μm to approximately 1 cm, depending on thetype of nerve cells in which said device may be implanted. The length ofthe device may vary depending on the extensiveness of a particularmedical condition. In some embodiments, the length of the device variesfrom approximately 2 μm to approximately 1 cm. In some otherembodiments, the housing 100 may be made from any electrostatic plasticmaterial such as cellophane or a more rigorous material like a diamond.According to one embodiment, the housing 100 is made from silica orprotein such as Bacteriorhodopsin or Rhodopsin.

The first end 115 and second end 116 of the housing 100 may have atleast two types of openings. In some embodiments, there are at least twoopenings of each type. In some other embodiments, the openings on thefirst end 115 of the housing 100 may be of the same size and shape, andthe openings on the second end 116 of the housing 100 may be of the samesize and shape.

In some preferred embodiments, the openings may vary in diameter. Theopenings of first type 101 may have a larger diameter than the openingsof the second type 102. In still other embodiments, the openings of thesecond type 102 may be present only on first end 115 of the housing 100.The openings of the first type 101 may have a larger diameter and mayserve for movement of cell material through the device which may permitto restore the anterograde and retrograde exchange of cell materialbetween the severed parts of a nerve.

The openings of the first type 101 on the first end 115 of the housing100 and the opening of the first type 101 on the second end 116 of thehousing 100 may merge or may be connected to hollow tubular extensions103 which may have the same diameter as the diameter of the openings ofthe first type 101. In some preferred embodiments, the openings of thefirst type 101 on the first end 115 of the housing 100 may be connectedwith the opening of the first type 101 located on the second side 116 ofthe housing 100 by a connective tube or a cavity of some other shape.Such unity of hollow tubular extension and the opening of the first type101 of the first end 115 of the housing 100 with a connective tube andthe opening of the first type 101 of the second end 116 of the housing100 may create a single cavity, which may be called a microfluidchannel. In some embodiments, the microfluid channel may be made as asingle form having a hollow inside, for example it may be in a form of atube, which may go through entire device. The length of the microfluidchannel may vary from 1 μm to 5 cm. The microfluid channel may allow forunimpeded traveling of cell material from the first end 115 of thesevered axon to the second end 116 of the severed axon.

The openings of the second type 102 on the first end 115 of the housing100 may have a smaller diameter and may serve to direct ions such assodium ions to enter the cavity of the housing 100. The ions may enter anerve cell at increased numbers during the depolarization stage of anaction potential. The openings of the second type 102 may merge or maybe connected to some hollow tubular extension 104, for example it may bea tube. A unity of the opening of the second type 102 and the hollowtubular extension 104 may be called an ion-guiding channel. In someembodiments, the ion-guiding channel may have the same diameter as thediameter of the openings of the second type 102.

The invention may further incorporate at least one rotating mechanism105 positioned within (or outside in another embodiment) the cavity ofthe housing 100. The rotating mechanism 105 may rotate within the cavityof the housing 100. The rotating mechanism 105 may be a turbine, shapedlike a cone, positioned such that the sharpest end may look inside thehousing 100. The rotating mechanism 105 may have needle-like protrusions106 which may be referred as micro-terminals. The micro-terminals maycarry an electric charge. The micro-terminals may be positioned to facethe second type 102 openings, or ion-guiding channels on the first end115 of the housing 100.

The needle-like protrusions 106, or micro-terminals, may be set at anangle of approximately thirty to approximately sixty degrees relativelyto the plane of the ion-guiding channels linked to the openings of thesecond type 102. In some preferred embodiments, the micro-terminals maybe positioned at approximately forty-five degrees relatively to theplane of the ion-guiding channels linked to the openings of the secondtype 102. The needle-like protrusions 106, or micro-terminals, may havethe same charge as the ions entering the housing 100 through theion-guiding channels.

In some preferred embodiments, the micro-terminals may carry positivecharge. During an action potential, sodium ions, which may enter thecell during the depolarization stage of the action potential, may bedirected by the ion-guiding channels toward the micro-terminals of therotating mechanism 105. Since sodium ions and the micro-terminals havethe same charge, the micro-terminals may be repelled away from theion-guiding channels. The process of repulsion may displace the rotatingmechanism 105 and bring about the rotation of the rotating mechanism105.

The invention may further incorporate at least one generator mechanism107 positioned within the cavity of the housing 100 and connected to therotating mechanism 105. For example, when rotating mechanism 105 mayhave shape of a cone, the generator mechanism 107 may be connected tothe sharpest end. In some preferred embodiments, the generator mechanism107 may represent a cluster of conducting wires rotating between thepoles of a magnet or an electromechanical motor such as a dynamo. Thedevice 100 may be self-powered. The term self-powered is intended toinclude many forms of power generation including dynamos, neuralactivity, magnetic, batteries or any combination thereof. It is alsoenvisioned that a power source external to the body may be utilize inaccordance with the present invention. By way of example, a braceletcontaining a battery may communicate with the device and act as agenerator or power generation means.

The displacement of the rotating mechanism 105 upon influx, or entry, ofsodium ions through the ion-guiding channels linked to the openings ofthe second type 102 may result in the rotation of the rotating mechanism105 which may result in movement of some part of the generator mechanism107 such as conducting wires around a magnet if the generator mechanism107 may consist of conducting wires and a magnet or a rotor in anelectromechanical motor if the generator mechanism 107 may consist of anelectromotor.

The rotation of a part of the generator mechanism 107 such as conductingwires or rotor may result in changes in magnetic field within thegenerator mechanism 107. In accordance with the Faraday laws, thesechanges may produce current within the generator mechanism 107, forexample in conducting wires or in a stator of an electromechanicalmotor. In some embodiments, the generator mechanism 107 may produceelectric potential from at least approximately 7 mV to approximately 60mV.

The invention may further incorporate a plurality of conductors 108 forcollecting and moving current from the generator mechanism 107. In someembodiments, there may be at least two conductors 108. Some of theconductors 108 may be connected to the cathode terminals of thegenerator mechanism 107 and some of the conductors 108 may be connectedto the anode terminals of the generator mechanism 107.

A single conductor may be a piece of a wire from any conducting materialsuch as copper. In some other preferred embodiments, the conductors 108may be made out of polyacytelene. In some still other preferredembodiments, the conductors 108 may be made in a shape of a tube ofmicro- or nano size. In certain embodiments, a conductor may be a partof electrochemical or other type of electrode-like systems that may beused to inject current into a nerve cell.

In some preferred embodiments, the conductors 108 may be attached to anerve ending in the proximity of the second side of the housing 100. Forexample, the conductors 108 which may be connected to the generatormechanism 107 located on the first side of the housing 100 may beattached to the nerve ending attached to the second side of the housing100.

The conductors 108 which may be connected to the cathode terminal andthe conductors 108 which may be connected to the anode terminal maycreate a voltage difference at the place of their attachment to thenerve ending. Such voltage difference may cause depolarization at thenerve ending and may provoke an action potential which may have same,similar, or different properties as the action potential arrived to theopposite side of said device.

For example, it may be assumed that Sodium ions enter a nerve cellduring action potential at a rate of 200 ions per a sec, that there maybe 1000 voltage gated channels per square micron of a membrane, and thatthe time of a single depolarizing event may be 1×10⁻³ seconds. For asegment of about 5 μm long and 20 μm wide, the surface area may beapproximately 314 μm² [2×π×10 μm×5 μm] which may suggest the presence ofapproximately 314,000 voltage gated channels. Based on the suggestednumber of channels, a single depolarizing effect may result in a combinecharge of about 1.0048×10⁻¹¹ C [314,000×200×1.6×10⁻¹⁹ C], where C standsfor Coulomb. The resulting charge may exert a force on the rotatingmechanism 105 of approximately 0.907 N [1×(4×π×ε₀)⁻¹×q₁×q₂×r⁻²]. Theapplication of such force on the rotating mechanism 105 may create atorque of 11.34 Nμm [T=r×F], where T stands for torque, r stands forradius, and F stands for force. If it may be assumed that the rotatingsystem weights about 350 μg, then the rotating system of such weight mayhave a moment of inertia of about 0.05 46875 μgμm [0.5×weight×r²]. Suchtorque and such inertia may results in an angular acceleration of 207.36rad/s² [torque/inertia]. If it may be assumed that the rotatingmechanism 105 may consists of four solenoids with 20 copper coils persolenoid and two magnets that may have a field strength of 0.01 Teslaper magnet; then, the rotation of the rotating mechanism 105 may resultin generator an absolute voltage of approximately 800 mV [−(4×20)×0.01Tesla/1 s]. Based on widely accepted understanding of characteristics ofan action potential, the generated by the device voltage may besufficient to provoke an active potential.

The method of reviving and maintaining a severed nerve tissue or abundle of nerves of a body may comprise the steps of: providing ahousing 100 for conducting and modulating neural response, the housinghaving a first end 115, a second end 116 and a cavity, wherein thecavity is interposed between the first end 115 and the second end 116and the first end 115 of the housing 100 has a plurality of openings and116 second end of the housing 100 has a plurality of openings; providingat least one conductor 108 in communication with at least one of thefirst end 115 and the second end 116 for collecting current, whereineach of the conductors 108 are adapted to attach to at least one firstnerve ending; and fluids are transported between the first nerve endingand the second nerve ending. The generator mechanism 107 may be inside(or outside) the cavity and triggers a generator event. The generatorevent may be an acoustic signal, an acoustic wavelength, electriccurrent, a chemical change, an acoustic signal. There may also be atleast one sensing mechanism, wherein the sensing mechanism senses achange in nerve and effects a change according to the nerve change. Thenerve change may be a change in polarity, current, signal, acoustic,electric, light frequency, photonics, chemical, physical, thermal changeand change in chemical concentration. The term “neural response” may bea change of polarity of a nerve (the nerve excites itself as a fuse, theneural impulse is a wave of ions). A neural response may also be theneural impulse traveling from the end of the nerve back to the brain. Ifthe nerve innervates and contracts a muscle, it may be said to haveaffected the movement of the muscle tissue. The step of transportingfluids may be through at least one pathway and the fluids may beintracellular. The fluids according to the present invention may be anybodily fluids including intracellular, interferon, stem cells andplasma. The fluids may also be stored in a reservoir and may be pumpedby a pumping mechanism. The term pathway is intended to include any pathin which fluids, electric, acoustic, or chemical signals may travel. Thepathway may, but is not limited to, include tubes, microtubes,microfluid channels or any other path.

In summary, the device of FIG. 1 may conduct and modulate nerve signalsfrom a primary end of severed nerve 109 to a secondary end of thesevered nerve 110 wherein the first end 115 of the device is connectedto a primary end of a severed nerve 109 and the second end 116 of thehousing 100 is connected to a secondary end of a severed nerve 110. Thefirst end 115 of the device 100 has a plurality of openings (e.g. 103,104) which may be of the same of varied sizes and shapes. There is alsoa rotating mechanism 105 positioned with a cavity of the housing 100,which rotates within the cavity. A generator mechanism 107 is positionedwithin the cavity and connected to the rotating mechanism 105, andgenerates electric current upon rotation of the rotating mechanism 105.Conductors 108 collect current from the generator mechanism 107. As suchneural signals are conducted between nerve cells.

In some preferred embodiments and methods of operation, the device madein accordance with the invention FIG. 1 may still incorporate variousmicro-electromechanical systems 120 (MEMS), such as a central processingunit (CPU), memory storage, a sensor, a modifier, or an integratedcircuit. In some embodiments, some or all of thesemicro-electromechanical systems may be attached to walls of the cavityof the housing 100 or may be attached to any part of the rotatingmechanism 105, generator mechanism 107, or microfluid channels. Incertain embodiments, there may be at least one CPU which may be inelectronic communication with at least one memory storage system whichmay allow CPU to perform more complex functions. Other embodiments mayhave at least one sensor MEMS device for measuring nerve signals bysensing the substantiality of changes occurring in different parts ofthe device. The sensor may be in communication with CPU or with theelectronic memory storage system. Still other embodiments may have atleast one modifier for modifying the device response to nerve signalssensed by the sensor. Still further embodiments, may have at least oneelectronic integrated circuit which may link all MEMS devices with eachother.

The sensor may be in communication with and sample the characteristicsof the rotating mechanism 105 of the device (or many rotatingmechanisms). In certain embodiments, the sensor may sample the generatedcurrent in the generator mechanism 107.

The modifier may adjust the characteristics of the rotating mechanism105. In some preferred embodiments, the modifier may adjust thecharacteristics of current produced by the generator mechanism 107.

In some preferred embodiments, the sensor may sample the rotationcharacteristics of said rotating mechanism 105. The sampled informationmay be analyzed, may be stored, or may be used to adjust the rotationcharacteristics of the rotating mechanism 105 which may bring about thegenerator mechanism 107 to adjust the generated current which may betransmitted along the conductors 108 to initiate an action potential ina nerve ending. In other preferred embodiments, in which the sensor maysample the characteristics of the current, the sampled information maybe analyzed, may be stored, or may be directly communicated to themodifier to adjust the characteristics of the current which thegenerator mechanism 107 may transmit along the conductors 108 toinitiate an action potential in a nerve ending.

In some preferred embodiments and methods of operation, the neuralbridge device made in accordance with the invention, FIG. 2, mayincorporate a housing 200 having a first end 215, a second end and acavity. The diameter of the housing may vary from approximately 1 μm toapproximately 1 cm, depending on the type of nerve cells in which saiddevice may be implanted. The length of the device may vary depending onthe extensiveness of a particular medical condition. In someembodiments, the length of the device varies from approximately 2 μm toapproximately 1 cm. In some other embodiments, the housing may be madefrom any electrostatic plastic material such as cellophane or morerigorous like a diamond.

The first and second ends of said the housing may have at least twotypes of openings. In some embodiments, there are at least two openingsof each type. In some other embodiments, the openings on the first endof the housing may be of the same size and shape, and the openings onthe second end of the housing may be of the same size and shape.

In some preferred embodiments, the openings may vary in diameter. Theopenings of first type 201 may have a larger diameter than the openingsof the second type 202. In still other embodiments, the openings of thesecond type may be present only on first end 215 of the housing. Theopenings of the first type may have a larger diameter and may serve formovement of cell material through the device which may permit to restorethe anterograde and retrograde exchange of cell material between thesevered parts of a nerve.

The openings of the first type on the first end 215 of the housing andthe opening of the first type on the second end 216 of the housing 200may merge or may be connected to hollow tubular extensions 203 which mayhave the same diameter as the diameter of the openings of the firsttype. In some preferred embodiments, the openings of the first type onthe first end 215 of the housing 200 may be connected with the openingof the first type located on the second side of the housing by aconnective tube or a cavity of some other shape. Such unity of hollowtubular extension 203 and the opening of the first type of the first end215 of the housing 200 with a connective tube and the opening of thefirst type of the second end 216 of the housing 200 may create a singlecavity, which may be called a microfluid channel. In some embodiments,the microfluid channel may be made as a single form having a hollowinside, for example it may be in a form of a tube, which may go throughentire device. The length of the microfluid channel may vary fromapproximately 1 μm to approximately 5 cm. The microfluid channel mayallow for unimpeded traveling of cell material from the first end 215 ofthe severed axon to the second end 216 of the severed axon.

The openings of the second type on the first end 215 of the housing mayhave a smaller diameter and may serve to direct ions such as sodium ionsto enter the cavity of the housing. The ions may enter a nerve cell atincreased numbers during the depolarization stage of an actionpotential. The openings of the second type may merge or may be connectedto some hollow tubular extension 204, for example it may be a tube. Aunity at the opening of the second type and the hollow tubular extension204 may be called an ion-guiding channel. In some embodiments, theion-guiding channel may have the same diameter as the diameter of theopenings of the second type.

The invention may further incorporate at least one rotating mechanism205 positioned within the cavity of the housing. The rotating mechanism205 may rotate within the cavity and along a longitudinal axis of thehousing. The rotating mechanism 205 may be a turbine, shaped like acone, positioned such that the sharpest end may look inside the housing.The rotating mechanism 205 may have needle-like protrusions 206 whichmay be referred to as micro-terminals. The micro-terminals may carry anelectric charge. The micro-terminals may be positioned to face thesecond type openings, or ion-guiding channels on the first end 215 ofthe housing 200.

The needle-like protrusions 206, or micro-terminals, may be set at anangle of approximately thirty to approximately sixty degrees relativelyto the plane of the ion-guiding channels linked to the openings of thesecond type. In some preferred embodiments, the micro-terminals may bepositioned at approximately forty-five degrees relatively to the planeof the ion-guiding channels linked to the openings of the second type(e.g. 204). The needle-like protrusions 206, or micro-terminals, mayhave the same charge as the ions entering the housing through theion-guiding channels.

In some preferred embodiments, the micro-terminals may carry positivecharge. During an action potential, sodium ions, which may enter thecell during the depolarization stage of the action potential, may bedirected by the ion-guiding channels toward the micro-terminals of therotating mechanism. Since sodium ions and the micro-terminals have thesame charge, the micro-terminals may be repelled away from theion-guiding channels. The process of repulsion may displace the rotatingmechanism 205 and bring about the rotation of the rotating mechanism205.

The invention may further incorporate at least one generator mechanism207 positioned within the cavity of the housing 200 and connected to therotating mechanism 205. For example, when rotating mechanism 205 mayhave shape of a cone, the generator mechanism 205 may be connected tothe sharpest end. In some preferred embodiments, the generator mechanism205 may represent a cluster of conducting wires rotating between thepoles of a magnet or an electromechanical motor such as a dynamo.

The displacement of the rotating mechanism 205 upon influx, or entry, ofsodium ions through the ion-guiding channels linked to the openings ofthe second type may result in the rotation of the rotating mechanism 205which may result in a movement of some part of the generator mechanism207 along a longitudinal axis of the housing such as conducting wiresaround a magnet if the generator mechanism 207 may consist of conductingwires and a magnet or a rotor in an electromechanical motor if thegenerator mechanism 207 may consist of an electromotor.

The rotation of a part of the generator mechanism 207 such as conductingwires or rotor may result in changes in magnetic field within thegenerator mechanism 207. In accordance with the Faraday laws, thesechanges may produce current within the generator mechanism 207, forexample in conducting wires or in a stator of an electromechanicalmotor. In some embodiments, the generator mechanism 207 may produceelectric potential from at least approximately 7 mV to approximately 60mV.

The invention may further incorporate a plurality of conductors 208 forcollecting and moving current from the generator mechanism 207. In someembodiments, there may be at least two conductors 208. Some of theconductors 208 may be connected to the cathode terminals of thegenerator mechanism 207 and some of said conductors may be connected tothe anode terminals of the generator mechanism 207.

A single conductor may be a piece of a wire from any conducting materialsuch as copper. In some other preferred embodiments, the conductors maybe made out of polyacytelene. In some still other preferred embodiments,the conductors may be made in a shape of a tube of micro- or nano size.In certain embodiments, a conductor may be a part of electrochemical orother type of electrode-like systems that may be used to inject currentinto a nerve cell.

In some preferred embodiments, the conductors may be attached to a nerveending in the proximity of the second side of the housing. For example,the conductors which may be connected to the generator mechanism locatedon the first side of the housing may be attached to the nerve endingattached to the second side of the housing.

The conductors which may be connected to the cathode terminal and theconductors which may be connected to the anode terminal may create avoltage difference at the place of their attachment to the nerve ending.Such voltage difference may cause depolarization at the nerve ending andmay provoke an action potential which may have same, similar, ordifferent properties as the action potential arrived to the oppositeside of said device.

In summary, the device of FIG. 2 may conduct and modulate nerve signalsfrom a primary end of severed nerve 209 to a secondary end of thesevered nerve 210 wherein the first end 215 to the device is connectedto the primary end of a severed nerve 209 and the second end of thehousing is connected to a secondary end of a severed nerve 210.

In some preferred embodiments and methods of operation, the device madein accordance with the invention FIG. 2 may still incorporate variousmicro-electromechanical systems (MEMS), such as a central processingunit (CPU), memory storage, a sensor, a modifier, or an integratedcircuit. The MEMS may be inside the device or outside the device. It mayalso be partially contained within the human body, such as anintravenous connection. In some embodiments, some or all of thesemicro-electromechanical systems may be attached to walls of the cavityof the housing or may be attached to any part of the rotating mechanism,generator mechanism, or microfluid channels. In certain embodiments,there may be at least one CPU which may be in electronic communicationwith at least one memory storage system which may allow CPU to performmore complex functions. Other embodiments may have at least one sensorMEMS device for measuring nerve signals by sensing the substantiality ofchanges occurring in different parts of the device. The sensor may be incommunication with CPU or with the electronic memory storage system.Still other embodiments may have at least one modifier for modifying thedevice response to nerve signals sensed by the sensor. Still furtherembodiments, may have at least one electronic integrated circuit whichmay link all MEMS devices with each other.

The sensor may sample the characteristics of the rotating mechanism ofthe device. In certain embodiments, the sensor may sample the generatedcurrent in the generator mechanism.

The modifier may adjust the characteristics of the rotating mechanism.In some preferred embodiments, the modifier may adjust thecharacteristics of current produced by the generator mechanism.

In some preferred embodiments, the sensor may sample the rotationcharacteristics of the rotating mechanism. The sampled information maybe analyzed, may be stored, or may be used to adjust the rotationcharacteristics of the rotating mechanism which may bring about thegenerator mechanism to adjust the generated current which may betransmitted along the conductors to initiate an action potential in anerve ending. In other preferred embodiments, in which the sensor maysample the characteristics of the current, the sampled information maybe analyzed, may be stored, or may be directly communicated to themodifier to adjust the characteristics of the current which thegenerator mechanism may transmit along the conductors to initiate anaction potential in a nerve ending.

In some preferred embodiments and methods of operation, the neuralbridge device made in accordance with the invention, FIG. 3, mayincorporate a housing 300 having a first end 315, a second end 316 and acavity. There may be a first device 301 (such as that depicted inFIG. 1) located in the first end 315 of the housing 300; and there maybe a second device 302 (such as that depicted in FIG. 1) located in thesecond end 316 of the housing 300. It is envisioned that the term deviceis interchangeable with the term neural bridge device and is intended todenote many different embodiments as depicted in the figures anddisclosed herein.

In some preferred embodiments, the first device 301 may be positionedhaving its first side of its housing 300, which may carry theion-guiding channels, looking at the primary end of a severed nerve 309.In addition, the second device 302 may be positioned having its firstside of its housing 300, which may carry the ion-guiding channels,looking at the secondary end of a severed nerve 310.

In certain embodiments, at least one hollow tubular extension on thesecond end of the first device 301 may be linked to at least one hollowtubular extension (e.g. 103) on the first end of the second device 302through hollow tubular extensions 303 having a cavity. In some othercertain embodiments, the hollow tubular extensions 303 may connect atleast one microfluid channel of the first device 301 with at least onemicrofluid channel of the second device 302. In some preferredembodiments, the hollow tubular extensions 303 may have a length fromapproximately 1 μm to approximately 5 cm. In some other preferredembodiments, the form may be shaped as a tube and may be referenced as amicrotube. The microtube may allow for unimpeded traveling of cellmaterial from the first end of the severed axon to the second end of thesevered axon. In still other preferred embodiments, the microtube may becomposed of any plastic material.

The device made in accordance with the invention FIG. 3 may stillincorporate various micro-electromechanical systems (MEMS), such as acentral processing unit (CPU), memory storage, a sensor, a modifier, oran integrated circuit. In some preferred embodiments, the first device301 on the first side 315 of the housing 300 and the second device 302on the second side 316 of the housing 300 may share the variousmicro-electromechanical systems. In still other preferred embodiments,the first device 301 on the first side of the housing 300 may have itsown set of various micro-electromechanical systems, and the seconddevice 302 on the second side of the housing 300 may have its own set ofvarious micro-electromechanical systems. Some or all of thesemicro-electromechanical systems may be attached to walls of the cavityof the housing 300 or may be attached to any part of the first device301, the second device 302, and or to microtubes 303. There may be atleast one CPU which may be in electronic communication with at least onememory storage system which may allow the CPU to perform more complexfunctions. There may be at least one sensor MEMS device for measuringnerve signals by sensing the substantiality of changes occurring indifferent parts of the device. The sensor may be in communication withCPU or with the electronic memory storage system. Still otherembodiments may have at least one modifier for modifying the deviceresponse to nerve signals sensed by the sensor. There may be at leastone electronic integrated circuit which may link all MEMS devices witheach other.

The sensor may sample the characteristics of the rotating mechanismlocated in the first device and the second device. The sensor may samplegenerated current at the generator mechanism of the first device and atthe generator mechanism of the second device.

The modifier may adjust the characteristics of rotating mechanism in thefirst device or the second device. In some preferred embodiments, themodifier may adjust the characteristics of generated current produced bythe generator mechanism located in the first device or in the seconddevice.

The sensor may sample the rotation characteristics of the rotatingmechanism. The sampled information may be analyzed, stored, or used toadjust the rotation characteristics of the rotating mechanism, in thefirst device or the second device, which may bring about the generatormechanism, in the first device 301 or in the second device 302, toadjust the generated current which may be transmitted along theconductors to initiate an action potential in a nerve ending. The sensormay sample the characteristics of the current, the sampled informationmay be analyzed, stored, or may be directly communicated to the modifierto adjust the characteristics of the current which the generatormechanism, in the first device or in the second device, may transmitalong the conductors to initiate an action potential in a nerve ending.

The neural bridge device, as depicted in FIG. 4, may incorporate ahousing 400 having a first end, a second end and a cavity. There may bea first device 401 of FIG. 2 located in the first end of the housing400; and there may be a second device 402 of FIG. 2 located in thesecond end of the housing 400.

In some preferred embodiments, the first device 401 may be positionedhaving its first side of its housing 400, which may carry theion-guiding channels, facing the first end of a severed nerve. Inaddition, the second device 402 may be positioned having its first sideof its housing 400, which may carry the ion-guiding channels, facing thesecond end of a severed nerve.

In certain embodiments, at least one hollow tubular extension on thesecond end of the first device 401 may be linked to at least one hollowtubular extension on the first end of the second device 402 through ahollow form 403 having a cavity. In some other certain embodiments, theform 403 may connect at least one microfluid channel of the first device401 with at least one microfluid channel of the second device 402. Insome preferred embodiments, the form 403 may have a length fromapproximately 1 μm to approximately 5 cm. In some other preferredembodiments, the form may be shaped as a tube and may be referenced as amicrotube. The microtube may allow for unimpeded traveling of cellmaterial from the first end of the severed axon to the second end of thesevered axon. In still other preferred embodiments, the microtube may becomposed of any plastic material.

In some preferred embodiments and methods of operation, the device madein accordance with the invention FIG. 4 may still incorporate variousmicro-electromechanical systems (MEMS), such as a central processingunit (CPU), memory storage, a sensor, a modifier, or an integratedcircuit. In some preferred embodiments, the first device 401 on thefirst side of the housing 400 and the second device 402 on the secondside of the housing 400 may share the various micro-electromechanicalsystems. In still other preferred embodiments, the first device 401 onthe first side of the housing 400 may have its own set of variousmicro-electromechanical systems, and the second device 402 on the secondside of the housing 400 may have its own set of variousmicro-electromechanical systems. Some or all of thesemicro-electromechanical systems may be attached to walls of the cavityof the housing 400 or may be attached to any part of the first device401, the second device 402, and or to microtubes 403. In certainembodiments, there may be at least one CPU which may be in electroniccommunication with at least one memory storage system which may allowCPU to perform more complex functions. Other embodiments may have atleast one sensor MEMS device for measuring nerve signals by sensing thesubstantiality of changes occurring in different parts of the device.The sensor may be in communication with CPU or with the electronicmemory storage system. There may be at least one modifier for modifyingthe device response to nerve signals sensed by the sensor. Still furtherembodiments, may have at least one electronic integrated circuit whichmay link all MEMS devices with each other.

The sensor may sample the characteristics of the rotating mechanismlocated in the first device and the second device. In certainembodiments, the sensor 405 may sample generated current at thegenerator mechanism of the first device and at the generator mechanismof the second device.

The modifier may adjust the characteristics of rotating mechanism in thefirst device or the second device. In some preferred embodiments, themodifier may adjust the characteristics of generated current produced bythe generator mechanism located in the first device or in the seconddevice.

In some preferred embodiments, the sensor may sample the rotationcharacteristics of said rotating mechanism. The sampled information maybe analyzed, may be stored, or may be used to adjust the rotationcharacteristics of the rotating mechanism, in the first device or in thesecond device, which may bring about the generator mechanism, in thefirst device or in the second device, to adjust the generated currentwhich may be transmitted along the conductors to initiate an actionpotential in a nerve ending. In still other preferred embodiments, inwhich the sensor may sample the characteristics of the current, thesampled information may be analyzed, may be stored, or may be directlycommunicated to the modifier to adjust the characteristics of thecurrent which the generator mechanism, in the first device or in thesecond device, may transmit along the conductors to initiate an actionpotential in a nerve ending.

In some preferred embodiments and methods of operation, the neuralbridge device made in accordance with the invention, FIG. 5, may consistof a first device 501 of FIG. 1 which may be positioned in the firstnerve ending and a second device 502 of FIG. 1 which may be positionedin the second nerve ending. In some further preferred embodiments, theremay be at least one microtube 503 connecting at least one hollow tubularextension on the second end of the first device 501 with at least oneextension on the second end of the second device 502. In certain otherpreferred embodiments, the microtube may be composed of any plasticmaterial.

In some preferred embodiments, the first device 501 may be positionedhaving its first side of its housing 500, which may carry theion-guiding channels, facing the first end of a severed nerve. Inaddition, the second device 502 may be positioned having its first sideof its housing 400, which may carry the ion-guiding channels, facing thesecond end of a severed nerve.

In some preferred embodiments and methods of operation, the neuralbridge device made in accordance with the invention, FIG. 6, may consistof a first device 601 of FIG. 2 which may be positioned in the firstnerve ending and a second device 602 of FIG. 2 which may be positionedin the second nerve ending. In some further preferred embodiments, theremay be at least one microtube 603 connecting at least one hollow tubularextension on the second end of the first device 601 with at least oneextension on the second end of the second device 602. In certain otherpreferred embodiments, the microtube may be composed of any plasticmaterial.

In some preferred embodiments, the first device 601 may be positionedhaving its first side of its housing 600, which may carry theion-guiding channels, facing the first end of a severed nerve. Inaddition, the second device 602 may be positioned having its first side615 of its housing 600, which may carry the ion-guiding channels, facingthe second end of a severed nerve.

The invention may further incorporate a method for modulating nervesignals. According to some embodiments of the invention, the device ofFIG. 1 carrying some or all of the MEMS devices which may be associatedwith certain embodiments of the device of FIG. 1 may be secured betweenthe first end of a severed nerve and the second end of a severed nerve.The desired signals may be communicated to the device by any suitablemeans. The device may modify receiving nerve signal in accordance withthe desired signals which may have been communicated to the device. Insome embodiments, the device may communicate the signals away from thedevice by any suitable means.

According to some embodiments of the invention, there may be at leasttwo devices of FIG. 1 secured between the first end of a severed nerveand the second end of the severed nerve, the desired signals may becommunicated to the devices by any suitable means, and the devices maymodify receiving nerve signal in accordance with the desired signalswhich may have been communicated to said devices. In some embodiments,the devices may communicate the signals away from the devices by anysuitable means. In some other embodiments, the devices may communicatethe desired signals among each other in synchronous or asynchronousmanner. In some other embodiments, the devices may modify nerveresponses outside a particular nerve cell containing one or many devicesof FIG. 1. In still other preferred embodiments, there may be acentralized controlling device implanted which may control thefunctionality of the devices of FIG. 1.

The invention may further incorporate a method for modulating nervesignals. According to some embodiments of the invention, the device ofFIG. 2 carrying some or all of the MEMS devices which may be associatedwith certain embodiments of the device of FIG. 2 may be secured betweenthe first end of a severed nerve and the second end of a severed nerve.The desired signals may be communicated to the device by any suitablemeans. The device may modify receiving nerve signal in accordance withthe desired signals which may have been communicated to the device. Insome embodiments, the device may communicate the signals away from thedevice by any suitable means. The term neural bridge device is intendedto include any of the various neural devices disclosed hereininterchangeably without limitation.

According to some embodiments of the invention, there may be at leasttwo devices of FIG. 2 secured between the first end of a severed nerveand the second end of the severed nerve, the desired signals may becommunicated to the devices by any suitable means, and the devices maymodify receiving nerve signal in accordance with the desired signalswhich may have been communicated to said devices. In some embodiments,the devices may communicate the signals away from the devices by anysuitable means. In some other embodiments, the devices may communicatethe desired signals among each other in synchronous or asynchronousmanner. In some other embodiments, the devices may modify nerveresponses outside a particular nerve cell containing one or many devicesof FIG. 2. In still other preferred embodiments, there may be acentralized controlling device implanted which may control thefunctionality of the devices of FIG. 2.

The invention may further incorporate a method for modulating nervesignals. According to some embodiments of the invention, the device ofFIG. 3 carrying some or all of the MEMS devices which may be associatedwith certain embodiments of the device of FIG. 3 may be secured betweenthe first end of a severed nerve and the second end of a severed nerve.The desired signals may be communicated to the device by any suitablemeans. The device may modify receiving nerve signal in accordance withthe desired signals which may have been communicated to the device. Insome embodiments, the device may communicate the signals away from thedevice by any suitable means.

According to some embodiments of the invention, there may be at leastseveral devices of FIG. 3 implanted into a human body, the desiredsignals may be communicated to the devices by any suitable means, andthe devices may modify receiving nerve signal in accordance with thedesired signals which may have been communicated to said devices. Insome embodiments, the devices may communicate the signals away from thedevices by any suitable means. In some other embodiments, the devicesmay communicate the desired signals among each other in synchronous orasynchronous manner. In some other embodiments, the devices may modifynerve responses outside a particular nerve cell containing one or manydevices of FIG. 3. In still other preferred embodiments, there may be acentralized controlling device implanted which may control thefunctionality of the devices of FIG. 3.

According to some embodiments of the invention, the device of FIG. 4 maybe carrying some or all of the MEMS devices which may be associated withcertain embodiments of the device and may be secured between the firstend of a severed nerve and the second end of a severed nerve. Thedesired signals may be communicated to the device by any suitable means.The device may modify receiving nerve signal in accordance with thedesired signals which may have been communicated to the device. In someembodiments, the device may communicate the signals away from the deviceby any suitable means.

There may several devices as depicted in FIG. 4 implanted into a humanbody and the desired signals may be communicated to the devices by anysuitable means. The devices may modify receiving nerve signal inaccordance with the desired signals which may have been communicated tosaid devices. In some embodiments, the devices may communicate thesignals away from the devices by any suitable means. In some otherembodiments, the devices may communicate the desired signals among eachother in synchronous or asynchronous manner. In some other embodiments,the devices may modify nerve responses outside a particular nerve cellcontaining one or many devices of FIG. 4. In still other preferredembodiments, there may be a centralized controlling device implantedwhich may control the functionality of the devices of FIG. 4.

The invention may further incorporate a method for modulating nervesignals. According to some embodiments of the invention, the device ofFIG. 5 carrying some or all of the MEMS devices which may be associatedwith certain embodiments of the device of FIG. 5 may be secured betweenthe first end of a severed nerve and the second end of a severed nerve.The desired signals may be communicated to the device by any suitablemeans. The device may modify receiving nerve signal in accordance withthe desired signals which may have been communicated to the device. Insome embodiments, the device may communicate the signals away from thedevice by any suitable means.

According to some embodiments of the invention, there may be severaldevices of FIG. 5 implanted into a human body, the desired signals maybe communicated to the devices by any suitable means, and the devicesmay modify receiving nerve signal in accordance with the desired signalswhich may have been communicated to said devices. In some embodiments,the devices may communicate the signals away from the devices by anysuitable means. In some other embodiments, the devices may communicatethe desired signals among each other in synchronous or asynchronousmanner. In some other embodiments, the devices may modify nerveresponses outside a particular nerve cell containing one or many devicesof FIG. 5. In still other preferred embodiments, there may be acentralized controlling device implanted which may control thefunctionality of the devices of FIG. 5.

According to one embodiment of the present invention, the device 600 asdepicted in FIG. 6, may carry some or all of the MEMS devices. Thedevice 600 may be secured between the primary end of a severed nerve 615and the secondary end of a severed nerve 616. The desired signals may becommunicated to the device 600 by any suitable means. The device 600 mayreceive and modify nerve signals in accordance with the desired signalswhich may have been communicated to the device. The device 600 maycommunicate the signals away from the device by any suitable means.

There may be several devices implanted into a human body, the desiredsignals may be communicated to the devices by any suitable means, andthe devices may modify receiving nerve signal in accordance with thedesired signals which may have been communicated to said devices. Insome embodiments, the devices may communicate the signals away from thedevices by any suitable means. In some other embodiments, the devicesmay communicate the desired signals among each other in synchronous orasynchronous manner. In some other embodiments, the devices may modifynerve responses outside a particular nerve cell containing one or manydevices of FIG. 6. In still other preferred embodiments, there may be acentralized controlling device implanted which may control thefunctionality of the devices of FIG. 6.

FIG. 7 depicts a method of restoring nerve signals, according to apreferred embodiment. The method may comprise the steps of: step 700securing a first end of a neural bridge device to the primary end ofsevered nerve cell. The term neural bridge is intended to include allvariants of the present invention devices. Step 702 securing a secondend of a neural bridge device to the secondary end of a severed nervecell. Step 704 may be modulating the nerve signal. Modulating a nervesignal may further comprise the steps of: step 706 communicating desiredsignals to the neural device, and step 708 modifying the received nervesignals by the neural bridge device based on the communicated signals.Step 710 may be communicating nerve signals outside a nerve cell. Step712 may be intercommunicating by a plurality of the devices. Step 713modifying nerve signals outside a particular nerve cell containing thedevice. The term maintaining includes sustaining, re-enabling,re-innervating, and maintaining the nerve.

As shown in FIG. 8-11, the housing 800 may contain pathways such asmicrotubes for transporting fluids from a first end 804 to a second end806. According to the example shown, there are two conductors 808 and810. The first conductor 808 is in communication with first end 804 andthe second conductor 810 is in communication with the second end 806. Asshown the fluids and electric, acoustic, and chemical signals travelbetween the first nerve ending 804 and the second nerve ending 806.There may also be a pumping means 814 for pumping the fluids.

As shown in FIG. 12, a system for communicating between at least twoneural bridge devices (100) for reviving and maintaining a severed nervetissue or a bundle of nerves of a body, the system comprising: at leasttwo neural bridge devices (e.g. 1000, 1002, 1004, 1006); at least oneneural bridge switch (e.g. 1008 and 1010), wherein each at least oneneural bridge switch (e.g. 1008 and 1010) is connected to at least oneneural bridge device (e.g. 1000, 1002, 1004 and 1006); at least oneneural bridge gateway (1012); at least one communication means (1014) incommunication with at least one neural bridge gateway (e.g. 1012) and atleast one neural bridge switch (e.g. 1008 and 1010). There may also be acalibrator (1022) in communication with the neural bridge gateway(1012). There may also be an external interface (1024). The Calibratoris an external device (a computer system) which communicates with theNeural Bridge Gateway that is implanted in a patient.

The neural bridge gateway (formerly called NeuroBioRouter or NBR) is adevice one or more of which will be implanted in a patient. The NeuralBridge Gateway interconnects multiple Neural Bridge Switches of theNeural Bridge Switch hierarchy for data communication. Datacommunication includes status, command and control communications andaction potentials. The Neural bridge Gateway may also act as anelectrical power distributor. The neural bridges directly connect toNeural bridge Switches not the Neural Bridge Gateway. The Neural BridgeGateway is programmable and connects the Neural Bridge Switch hierarchyto the external Calibrator. Neural bridges and Neural bridge switchesmay be programmable and programmed per-individual as part of theanalysis done by the Calibrator via the Neural Bridge Gateway. Once thestimulus/response articulation is satisfactory, the calibrator gauges itagainst a set of pre-determined values and threshold ranges, and burnsthe parameters to the Neural Bridge and Neural Bridge Switch Microchips.

Communication between the Calibrator and Neural Bridge Gateway may usewireless or wired technology. The Calibrator, according to a preferredembodiment, is external to the body. Via the Neural Bridge Gateway, theCalibrator is capable of communicating with each Neural Bridge andNeural Bridge Switch (also called a NeuroBioController or controller) inthe patient. Neural Bridges, Neural Bridge Switches, and Neural BridgeGateways may be programmable and able to report status and acceptcommands from the Calibrator. The Calibrator's software will determinethe functional connectivity of each Neural Bridge and store theresulting neural repair profile in its database. Under direction of themedical technical operator while connected to the patient undergoingrehabilitation, the Calibrator's software will command the setting ofappropriate parameters and functions in the Neural Bridges and NeuralBridge Switches for optimal repair of the neural injury. Once thestimulus/response articulation is satisfactory, the Calibrator gauges itagainst a set of pre-determined values and threshold ranges, and burnsthe parameters to the Neural Bridge and Neural Bridge Switch microchips.The Calibrator will be able to store, retrieve, and compare the neuralrepair profiles from multiple patients as well as neural functionprofiles from healthy patients. The Calibrator will be able to compareneural repair profiles taken at different times from the same patient.The Calibrator may include a power source to recharge (through thepatient's skin; wired or wirelessly) the rechargeable battery of theNeural Bridge Gateway. The Calibrator leads to the construction of aNeural Routing Table in the Neural Gateway. These routing tables arestatic routes and are developed under direction of the medical technicaloperator while connected to the patient/user undergoing rehabilitation;the Calibrator's software will command the setting of appropriateparameters and functions for restoring neural activity. The NeuralGateway will also poll Neural Switches, Neural Bridges, Sensory mesh,Sensory Interface Chips, actuator interface chips, and third partyelectromechanical actuator devices for up/down status of all devices inthe network using Neural Signaling Protocol (NSP). The Neural Gatewaywill have the capability to program routing around faults usingsecondary routes with NSP. The NSP gives the Neural Gateways capabilityto communicate with implanted components including Neural BridgeSwitches, Neural Bridges and Neural Bridge Gateways Sensory mesh,Sensory Interface Chips, actuator interface chips, and third partyelectromechanical actuator devices, using their Neural Addresses. Inthis way, the programmable neural bridge gateway routes data through atleast one component according to a desired path. For example, there maybe a number of sensory interface chips, and one may not be workingproperly. The programmable neural bridge gateway way effectively shutdown that sensor and route data around it. The actuator interface chiprefers to an integrated circuit that is between a prosthetic and one ofthe components (according to a preferred embodiment the neural bridge).

The neural bridge switch (e.g. 1008 and 1010) may be an integratedcircuit and is typically implanted. The neural bridge switch may also bewritable and programmable. When programmable, neural bridge witches maybe programmed by the calibrator through the neural bridge gateway andmay even be programmed through intermediate neural bridge switches.Programmable neural bridges may be programmed in this same manner,through their interconnections with neural bridge switches. The neuralbridge switch may also provide a table of locations of the neuralbridges and other neural bridge switches. Because there is more than oneneural bridge device, the neural bridge switch can also reroute aroundfaults. Each of the switches may be connected in a flexible hierarchyand may communicate with each other via a communication means. Thecommunication means may be any method of communicating betweenmicroprocessor known in the art. Wireless communication may includeBluetooth, infrared, WiFi.

There may also be a memory unit in communication with the integratedcircuit. The integrated circuit may control the communication means andthe memory unit. The integrated circuit may be in communication with amemory unit, which may be stored internally or externally. The memoryunit may even be a personal computer and may store functions or plannedmovements (such as in the case of physical therapy it may be useful totrack movement and use of a prosthetic). The neural bridges and theneural bridge switches may be programmed for the individual. The neuralbridge may also pass intracellular fluids between neural bridges via apump, provide distribution of electrical power, recharge an implantedbattery. Also, neural bridges may increase or decrease an axon'seffective rate of firing or modify action potentials. The neural bridgeswitch may direct the neural bridges and interface an integrated circuitto encode sensory stimuli for transmission to neural bridges through aneural bridge switch hierarchy. The neural bridge switch may also encodeaction potentials for transmission from neural bridges to the actuatordevices through the hierarchy. Also, the calibrator may be used tocalibrate movements and programming. The calibrator may also provideanalysis. Once the stimulus/response articulation is satisfactory, thecalibrator may gauge against a set of pre-determined values andthreshold ranges and burn (or program) the parameters to the neuralbridge and neural bridge switch integrated circuits. The neural bridgeswitch (1008, 1010) may also have a power supply (1016) which may beinternal or external. There may also be a fluid pump for pumping fluids(1018). The neural bridge switch (1008 and 1010) may also have a fluidpump (1026). Each of the fluid pumps may be neurochemical fluid pumps.

There may be a sensory mesh (1028) in communication with an integratedcircuit (1030). The sensory mesh may be, for example, artificial skinthat lays on top (or below) a prosthetic limb. Another example may besensory mesh that lays on top or below damaged skin, as shown in FIGS.14 and 15. If the sensory mesh lays on top of a prosthetic limb, thesensory mesh is made of a polymer that is flexible and durable. Thesensory mesh may (1034) be a fishnet-like structure composed of varioustransducers, spanning an arbitrary surface on the human skin It may alsobe shaped to look like a curvature, cylinder, or made to resemble awhole limb (1036). Every nexus point, where “nexus point” is a pointwhere two or more lines of the mesh intersect or join, is equipped witha sensor. This sensor may exist as part of a nexus or compose the nexusitself. The mesh network can be as granular as a micro- or nano-meteropenings or as wide as the one shown in FIG. 14. The mesh network can besymmetric or asymmetric in terms of sensor positioning. The abovepicture shows an asymmetric mesh. The sensory mesh can be endodermic(within the skin) or exodermic (on top of the skin) depending on theinjury and condition of the patient. The sensory mesh can also coexistwith a whole artificial limb, providing thermal, pressure sensory(transducer) and various sensory indicators as well as proprioception.The mesh must be composed of a flexible, biocompatible material. Themesh can be glued with a bio-adhesive either to the surface or beneaththe surface of the skin, or it can be surgically attached to it. In oneembodiment, the mesh can be composed of organo-metallic conductormaterial for the nexus interconnects, and its sensor components can becomposed of titanium, the whole mesh can then be coated in a hydrophobiccompound to prevent tissue interaction. Each nexus at the sensory meshserves as a “plug-in” point of the neural bridge, neural switch, or anyother device. The neural devices then collect and compute the data fromthe sensors and stimulate the correct neural pathways. Once thiscomputation is complete, the patient will decide, based on the stimulus,what action to take (move hand away from the stove, blow finger becausehe burned himself, or continue enjoying the warm waters of the ocean).FIG. 16 depicts the neural interaction with the sensory mesh. FIG. 16 isalso intended to depict a hierarchy of the sensory mesh. Transducers(such as sensors 2002) are at the surface, either in a mesh formation orin a “plastic microcircuit glove” formation-then neural bridges (orconnectors 2004) beneath-then switches (2006) which the neural bridges(2010) plug into-then a hierarchy of switches and neural bridges. Thefunction of the Sensory Interface Chip (2000) is to translate signalsfrom transducers such as heat, cold, etc. into signal pattern that thebrain can recognizes being heat, cold, and others. The Sensory Chip(2000) will perform translations between the various Transducers andBrain. The Sensory Interface Chip (2000) and sensory mesh (2012) may beprogrammable and programmed per-individual as part of the analysis doneby the Calibrator via the Neural Bridge Gateway (2008) and Neural BridgeSwitches (2006). The Sensory Interface Chip (2000) and sensory mesh(2012) are writable and programmable. When programmable, they areprogrammed by the Calibrator through the Neural Bridge Gateway (2008)and Neural Bridge Switches (2006). Interconnection between the SensoryInterface Chip (2000) and the Neural Bridge Switch (2006) for datacommunication (for status, command, control, artificial actionpotentials, and software download), and for optional electrical powerdistribution. The Sensory Interface Chip (2000) has the following datastores: table of locations of the sensory mesh nodes, sensory interfacechips, and neural bridge switches; capability to reroute around faults;check status of the sensory mesh and Sensory Interface Chips; ability tosave status and counters for later retrieval; addressability: one ormore level of addressing (physical and logical/functional) of sensorymesh and Sensory Interface Chips. Addressing is used for datacommunication; Optional Distribution of electrical power to sensorymesh; Optional implanted battery, optionally rechargeable through theNeural Bridge Gateway.

The following are possible steps of the Sensory System according to thepresent invention: transducers reacted to stimuli such as heat, cold,pressure, tactile and other environmental conditions, then generatesignals (analog/digital) to Sensory Interface Chip. The SensoryInterface Chip receives signals from various transducers and translatesthose signals from the sensory mesh to standardized digital signals forinput to the Neural Bridge Switch. The Neural Bridge Switches deliversthose signals to one or more Neural Bridges. The Neural Bridges whichconnect to severed axons and send action potentials toward the spinalcord and brain.

The sensory mesh may be fitted with the following transducers:mechanotransducer respond to mechanical stress or mechanical strain;thermotransducer respond to temperature, either heat, cold or both;phototransducer respond to light; barotransducer respond to pressure;csmotransducer may respond to the osmolarity of fluids (such as in thehypothalamus); propriotransducer provide the sense of position;nocinransducer respond to noxious or potentially noxious stimuli;hydrotransducer respond to changes in humidity; chemotransducer respondto chemical stimuli. The sensory mesh may connect (either wired orwirelessly) to the implanted Sensory Interface Chip (integrated circuit1030). There may be an attachment means which may be made frombiocompatibility polymer, wire, organo-metallic conductor, or anyconductive material which can conduct and relay digital or analogsignals. The Sensory Interface Chip (1030) connects to the sensory mesh(1028) and to the Neural Bridge Switch (1004). The Sensory InterfaceChip (1030) translates various sensory signals from the sensory mesh tostandardized digital signals for input to a second location, forexample, the Neural Bridge Switch. The hierarchy of Neural BridgeSwitches delivers those signals to one or more Neural Prosthetic(bridge), which connect to severed axons and send action potentialstoward the spinal cord and brain. The standardized digital signal mayalso be sent to an internal or external memory unit, which in turn maysend a directive through a standardized digital signal to a thirdlocation (such as a neural bridge switch, neural bridge, axon, brain,etc.). The sensory interface chip and sensory mesh may be programmableand programmed per the individual and their needs.

If the sensory mesh is implanted below the skin; the sensory mesh may bemade of Biocompatibility polymer. It may be fitted, for example, withthe following transducers: mechanoTransducer respond to mechanicalstress or mechanical strain; thermotransducer respond to temperature,either heat, cold or both; phototransducer respond to light;barotransducer respond to pressure; osmotransducer respond to theosmolarity of fluids (such as in the hypothalamus); propriotransducerprovide the sense of position; nocitransducer respond to noxious orpotentially; noxious stimuli; hydrotransducer respond to changes inhumidity; chemotransducer respond to chemical stimuli. The sensory meshconnects (either wired or wirelessly) to the implanted Sensory InterfaceChip. The Sensory Interface Chip connects to the sensory mesh and to theNeural Bridge Switch. The Sensory Interface Chip translates varioussensory signals from the sensory mesh to standardized digital signalsfor input to the Neural Bridge Switch. The hierarchy of Neural BridgeSwitches delivers those signals to one or more Neural Prosthetic(bridge), which connect to severed axons and send action potentialstoward the spinal cord and brain. There may also be, as shown in FIG.14, an electromechanical actuator in communication with integratedcircuit.

It should be understood that the foregoing relates to preferredembodiments of the invention and that modifications may be made withoutdeparting from the spirit and scope of the invention as set forth in thefollowing claims.

1. A device for communicating data between at least one of nerve cellendings, transducers and attachments said device comprising: at leastone programmable neural bridge device; at least one programmable neuralbridge switch, wherein each said at least one programmable neural bridgeswitch is an implanted integrated circuit and is connected to at leastone programmable neural bridge device; at least one programmable neuralbridge gateway; at least one communication means in communication withsaid at least one programmable neural bridge gateway and at least onesaid programmable neural bridge switch; and at least one externalcalibrator in communication with said at least one neural bridgegateway.
 2. A device as in claim 1, wherein said at least oneprogrammable neural bridge gateway routes data according to a desiredpath.
 3. A device as in claim 1, further comprising: at least oneprogrammable sensory interface integrated circuit in communication withsaid at least one programmable neural bridge switch; at least onetransducer in communication with said at least one sensory interfaceintegrated circuit; and at least one attachment means in communicationwith said at least one transducer.
 4. A device as in claim 3, whereinsaid sensory interface integrated circuit receives at least one sensorysignal from said transducer and translates said signal to at least onestandardized digital signal.
 5. A device as in claim 4, wherein said atleast one standardized digital signal is input to said at least oneprogrammable neural bridge switch.
 6. A device as in claim 5, whereinsaid at least one standardized digital signal is transferred from saidat least one programmable neural bridge switch to at least oneprogrammable neural bridge.
 7. A device as in claim 5, wherein saidprogrammable neural bridge is programmed according to analysis from saidcalibrator through said neural bridge gateway signal.
 8. A device as inclaim 1, wherein said external calibrator determines a satisfactorystimulus response articulation and provides parameters according to saidsatisfactory stimulus response articulation.
 9. A device as in claim 1,wherein said transducer senses a change in nerve state and effects aresponse according to said change in nerve.
 10. A system as in claim 9,wherein said change in nerve state is selected from the group consistingof polarity, current, signal, acoustic, electric, light frequency,photonics, chemical, physical, thermal change and change in chemicalconcentration.
 11. A system as in claim 1, wherein said transducer isselected from the group consisting of MechanoTransducer,thermotransducer, phototransducer, barotransducer, osmotransducer,propriotransducer, nocitransducer, hydrotransducer and chemotransducer.12. The device as in claim 1, further comprising a memory unit incommunication with said communication means.
 13. The device as in claim1, further comprising at least one external interface.
 14. The device asin claim 1, further comprising at least one electromechanical actuatorin communication with said integrated circuit.
 15. The device as inclaim 3, wherein said sensory interface integrated circuit is programmedaccording to input received from an input device.
 16. The device as inclaim 15, wherein said input device is selected from the groupconsisting of calibrator, microprocessor, computer and mobile device.17. A processor implemented method of communicating data between atleast one of nerve cell endings, spinal cord, brain and neural signalsof a user, said method comprising the steps of: providing at least oneprogrammable neural bridge device; providing at least one programmableneural bridge switch, wherein each said at least one programmable neuralbridge switch is an implanted integrated circuit and is connected to atleast one programmable neural bridge device; providing at least oneprogrammable neural bridge gateway; providing at least one communicationmeans in communication with said at least one programmable neural bridgegateway and at least one said programmable neural bridge switch;providing at least one external calibrator in communication with saidprogrammable neural bridge gateway; providing at least one sensoryinterface integrated circuit in communication with said at least oneprogrammable neural bridge switch; providing at least one transducer incommunication with said at least one sensory interface integratedcircuit; providing at least one attachment means in communication withsaid at least one transducer, wherein at least one said sensoryinterface integrated circuit receives at least one sensory signal fromsaid transducer and translates said signal to at least one standardizeddigital signal; determining a satisfactory stimulus responsearticulation to said at least one standardized digital signal; providingparameters according to said satisfactory stimulus responsearticulation; and programming said parameters on said programmableneural bridge.
 18. A method as in claim 17, further comprising the stepof communicating said at least one standardized digital signal to asecond location.
 19. A method as in claim 18, wherein said secondlocation is selected from the group consisting a neural bridge switch, aneural bridge, an axon, the spinal cord of the user, the user's brain,an external memory unit, an internal memory unit.
 20. A method as inclaim 17, further comprising the step of communicating a directivebetween said neural bridge switches, wherein said at least two saidneural bridges switches are connected in a flexible hierarchy.
 21. Amethod as in claim 17, further comprising the step of sensing a changein nerve state.
 22. A method as in claim 21, further comprising the stepof effecting a neural response according to said change in nerve state.23. A method as in claim 17, further comprising the step of: sending adirective by a standardized digital signal to a third location.
 24. Amethod as in claim 17, further comprising the step of: routing dataaccording to a desired path.